Abstract: A method for recording a magnetic resonance image dataset includes providing a magnetic resonance sequence with a series of sequence blocks, and providing at least one correction term to compensate for a magnetic field change. The magnetic field change is produced as a change of an actual magnetic field compared to a setpoint magnetic field by gradient pulses. The magnetic field change is established via a transfer characteristic of the gradient system of the magnetic resonance installation. The at least one correction term is used to compensate for the magnetic field change, and at least one magnetic resonance image dataset is recorded with the magnetic resonance sequence using the correction term.

Abstract: A method for recording a magnetic resonance image data set includes providing a magnetic resonance sequence. The magnetic resonance sequence includes at least one radio-frequency pulse and a slice-selection gradient pulse applied during or before the radio-frequency pulse, which is configured as non-constant. The method includes providing at least one correction term for compensating a magnetic field change of the slice-selection gradient pulse. The magnetic field change is ascertained via a transfer characteristic of the gradient system of the magnetic resonance system. The method also includes recording at least one magnetic resonance image data set with the magnetic resonance sequence using the correction term.

Abstract: A method for recording a magnetic resonance image dataset includes providing a magnetic resonance sequence with a series of sequence blocks, and providing at least one correction term to compensate for a magnetic field change. The magnetic field change is produced as a change of an actual magnetic field compared to a setpoint magnetic field by gradient pulses. The magnetic field change is established via a transfer characteristic of the gradient system of the magnetic resonance installation. The at least one correction term is used to compensate for the magnetic field change, and at least one magnetic resonance image dataset is recorded with the magnetic resonance sequence using the correction term.

Abstract: A method for recording a magnetic resonance image data set includes providing a magnetic resonance sequence. The magnetic resonance sequence includes at least one radio-frequency pulse and a slice-selection gradient pulse applied during or before the radio-frequency pulse, which is configured as non-constant. The method includes providing at least one correction term for compensating a magnetic field change of the slice-selection gradient pulse. The magnetic field change is ascertained via a transfer characteristic of the gradient system of the magnetic resonance system. The method also includes recording at least one magnetic resonance image data set with the magnetic resonance sequence using the correction term.

Abstract: A gradient system characterization function (e.g., a gradient system transfer function) may be developed by measuring a behavior of the MR device at a target temperature and developing at least one gradient system characterization function for a gradient coil of a magnetic resonance (MR) device at the target temperature based on the measured behavior. A patient may be subsequently imaged by the MR device, wherein the imaging process comprises measuring a temperature of a gradient coil, determining a gradient system characterization function at the measured temperature, calculating a pre-emphasized gradient of the gradient coil, and imaging the patient using the pre-emphasized magnetic field component.

Abstract: The disclosure relates to methods, devices, and systems for developing gradient system characterization functions and imaging a patient using pre-emphasized magnetic field components in a magnetic resonance (MR) device, wherein the processes allow for a reduction in a number of artifacts when reconstructing the magnetic resonance image. The gradient system characterization function (e.g., a gradient system transfer function) may be developed by measuring a behavior of the MR device at a target temperature and developing at least one gradient system characterization function for a gradient coil of the MR device at the target temperature based on the measured behavior.

Abstract: In a method and magnetic resonance (MR) apparatus for data acquisition with fat-water separation in a resulting MR image, an MR data acquisition sequence is operated to acquire MR signals from a subject. Said MR signals comprise fat signals originating from fat in the subject and water signals originating from water in the subject, are acquired by executing a frequency-modulated balanced steady-state free-precession (bSSFP) sequence. The MR signals are entered as numerical values into a memory organized as k-space, the memory thereby containing k-space data. An image is reconstructed from the k-data and subjected to regional phase correction. The corrected image being composed of respective pixels having an intensity produced by the fat signals and an intensity produced by the water signals, with the respective pixels being readily distinguishable from each other in the image due to use of the frequency-modulated bSSFP sequence and the block regional correction.

Abstract: In a magnetic resonance (MR) method and apparatus, an image reconstruction algorithm is used to reconstruct image data from k-space data that represent an acquired MR signal, and the reconstruction algorithm makes use of a model that requires the MR signal to exhibit a signal behavior from a relaxation model. In order to permit the reconstruction algorithm to be used when the acquired MR signal does not exhibit the model signal behavior due to motion of the subject, the k-space data are motion-corrected so as to produce corrected k-space data that represent said model signal behavior, and image data are reconstructed from the corrected k-space data using the reconstruction algorithm.

Abstract: In a method and magnetic resonance (MR) apparatus for data acquisition with fat-water separation in a resulting MR image, an MR data acquisition sequence is operated to acquire MR signals from a subject. Said MR signals comprise fat signals originating from fat in the subject and water signals originating from water in the subject, are acquired by executing a frequency-modulated balanced steady-state free-precession (bSSFP) sequence. The MR signals are entered as numerical values into a memory organized as k-space, the memory thereby containing k-space data. An image is reconstructed from the k-data and subjected to regional phase correction. The corrected image being composed of respective pixels having an intensity produced by the fat signals and an intensity produced by the water signals, with the respective pixels being readily distinguishable from each other in the image due to use of the frequency-modulated bSSFP sequence and the block regional correction.

Abstract: In a magnetic resonance (MR) method and apparatus, an image reconstruction algorithm is used to reconstruct image data from k-space data that represent an acquired MR signal, and the reconstruction algorithm makes use of a model that requires the MR signal to exhibit a signal behavior from a relaxation model. In order to permit the reconstruction algorithm to be used when the acquired MR signal does not exhibit the model signal behavior due to motion of the subject, the k-space data are motion-corrected so as to produce corrected k-space data that represent said model signal behavior, and image data are reconstructed from the corrected k-space data using the reconstruction algorithm.

Abstract: In a method for magnetic resonance imaging, k-space is sampled using density weighted data acquisition or acquisition weighted data acquisition, with at least one region of k-space being intentionally undersampled with respect to the Nyquist criterion. Reconstruction of the MR image is performed using a parallel imaging method, with the influence in the reconstructed image of the missing k-space data, as a result of the undersampling, being reduced.

Abstract: In a method for magnetic resonance imaging, k-space is sampled using density weighted data acquisition or acquisition weighted data acquisition, with at least one region of k-space being intentionally undersampled with respect to the Nyquist criterion. Reconstruction of the MR image is performed using a parallel imaging method, with the influence in the reconstructed image of the missing k-space data, as a result of the undersampling, being reduced.

Abstract: Example systems, methods, and apparatus associated with conjugate symmetry in parallel imaging are provided. One example method includes controlling a parallel magnetic resonance imaging (pMRI) apparatus to acquire a first magnetic resonance (MR) signal from a first point in k-space using a phased array of receiving coils. The method also includes identifying a second point in k-space that is related to the first point by a conjugate symmetry relation. The relation may be, for example, a reflection, a rotation, and so on. The method also includes determining a second MR signal associated with the second point based, at least in part, on the first MR signal and the conjugate symmetry relation and then reconstructing an MR image based, at least in part, on both the first MR signal and the second MR signal.

Abstract: Example systems, methods, and apparatus associated with conjugate symmetry in parallel imaging are provided. One example method includes controlling a parallel magnetic resonance imaging (pMRI) apparatus to acquire a first magnetic resonance (MR) signal from a first point in k-space using a phased array of receiving coils. The method also includes identifying a second point in k-space that is related to the first point by a conjugate symmetry relation. The relation may be, for example, a reflection, a rotation, and so on. The method also includes determining a second MR signal associated with the second point based, at least in part, on the first MR signal and the conjugate symmetry relation and then reconstructing an MR image based, at least in part, on both the first MR signal and the second MR signal.